JP2012526301A - Reduction of ophthalmic lenses and accommodation errors - Google Patents

Abstract

  The ophthalmic lens provides visual acuity that is clearly visible at both near and near viewing distances, and presents a near vision defocus image to the lens wearer at both near and near viewing distances. The ophthalmic lens of the present invention is used for the purpose of reducing an eye adjustment error of a lens wearer by various methods. The method for manufacturing an ophthalmic lens of the present invention is described.

Description

  This application is based on the provisions of 35 USC 119 (e) (35 USC § 119 (e)), US Patent Provisional Application No. 61 / 175,201, filed earlier on May 4, 2009. Although claimed in priority, the entirety of such prior application is hereby incorporated by reference herein.

  The present invention relates to an ophthalmic lens and various methods such as an ophthalmic lens manufacturing method and an ophthalmic lens usage method. More specifically, an ophthalmic lens and method for reducing ocular accommodation errors are disclosed, and a method for manufacturing such an ophthalmic lens is disclosed.

  Myopia or myopia affects a significant proportion of the world population, especially in some Asian countries. As a rule, myopia is accompanied by an unusually long extension of the human eye axis. With an axially elongated eyeball, the retina comes out of the "normal" focal plane, and the far-field object's image point is not located on the retina surface but is placed in front of the retina. . Those whose axially elongated eyeballs are involved in myopia to a greater extent may involve retinal detachment, glaucomatous disorders, degenerative myopic retinal disorders, and the like.

  Efforts have been made to alleviate the progression of myopia. Specific examples include the use of multifocal spectacles or multifocal contact lenses, the use of lenses that affect optical aberrations, the treatment of corneal shaping, the use of pharmacological agents, etc. There is. A number of ophthalmic lenses have already been disclosed to alleviate the progression of myopia, and these lenses are out of focus at both the vision correction range and the near vision distance, which provide vision that is clear at both near and far vision distances. And a myopic defocus area that provides an image. Specific examples of the difficulties associated with the goal of alleviating the progression of myopia for some of the previously proposed attempts include drug side effects, discomfort, vision recovery that is only a product of compromise, or Various combinations are mentioned.

  New methods or new uses for any ophthalmic lens have been invented. The ophthalmic lens of the present invention includes a vision correction area and a myopic defocus area. By using the ophthalmic lens of the present invention, reduction or reduction of the eye accommodation error is achieved. In other words, by providing the lens of the present invention, the lens wearer can demonstrate that the eye adjustment error in one or both eyes is reduced compared to one or both eyes not wearing the lens. Specific examples include reduction of the eye adjustment lag, reduction of the eye adjustment lead, or both.

  In one aspect, a method is provided for reducing an eye accommodation error in a patient capable of performing eye accommodation. Such methods include providing an ophthalmic lens that is deployed to a patient's eye. The ophthalmic lens includes or is provided with a vision correction area and a myopic defocus area. The details of the ophthalmic lens will be further described here. The lenses are provided to lens distributors, vision correctors, patients, or various combinations thereof. If the lens is a contact lens, the patient can place the lens in the patient's eye and the adjustment error is reduced compared to the eye adjustment error observed without the lens in the eye. Can be observed. If the lens is a spectacle lens, the patient can place the lens in the vicinity of the patient's eye and there is an adjustment error compared to the eye adjustment error observed without the lens in the vicinity of the eye. You can observe it being reduced.

  In another aspect, a method for producing an ophthalmic lens is provided. Such a method includes the step of forming a lens-forming material into an ophthalmic lens as described herein.

  In another aspect, applications of various lenses or lens forming materials are provided. For example, aspects of the present invention relate to a novel application of the ophthalmic lens of the present invention aimed at reducing the patient's eye accommodation error that can be accommodated. It is speculated that the patient needs to improve adjustment error. Another aspect of the present invention is that, as described herein, in the manufacture of an ophthalmic lens, a lens design aimed at reducing eye accommodation error for a patient capable of eye accommodation. It relates to the use.

  Each aspect of the invention is also set forth in the appended claims.

  Various embodiments of the present invention will be described in detail in the “Detailed Description” section below. As will be apparent from the context, the present specification, and the knowledge of those skilled in the art, any feature described in this document, or any combination of features, is included in such combinations. So long as the features do not contradict each other, they are within the scope of the present invention. Furthermore, no feature or combination of various features is specifically excluded from any embodiment of the present invention. Other advantages and aspects of the present invention are apparent in the following detailed description, the accompanying drawings, and the appended claims.

FIG. 1 is a front plan view of a first embodiment of an ophthalmic lens used in the method of the present invention. FIG. 2 is a front plan view of a second embodiment of an ophthalmic lens used in the method of the present invention. FIG. 3 is a graph illustrating eye accommodation error as a function of target distance.

  The method and application of the present invention is involved in certain ophthalmic lenses, compared to ophthalmic errors seen in patients who have been inspected with far corrected vision even when the ophthalmic lens is not worn. Also, the ophthalmic lens is involved in the ability to further reduce the adjustment error of the lens wearer's eyes. By implementing the methods and applications disclosed herein, the eye adjustment error is reduced and the adjustment accuracy is improved. Changes in eye accommodation error may be observed by a vision examiner such as an optometrist or an ophthalmologist, but measures eye accommodation error, records accommodation error, analyzes accommodation error data, or You may make it observe with the machine comprised so that processing of these various combinations may be performed. In addition, adjustment accuracy may be observed by a quantifiable measurement of improved visual performance, improved visual acuity, or other visual enhancement by the patient or lens wearer.

  With regard to the present disclosure, the “ophthalmic lens” means a lens that is installed in the vicinity of the patient's eye for the purpose of improving the visual performance of the patient. For example, the ophthalmic lens may be a contact lens placed on the cornea of the eye, an intraocular lens placed in the eye, or a corneal onlay placed between the corneal epithelium of the eye and the corneal matrix. It may be a lens, a corneal inlay lens placed in the corneal matrix of the eye, or a spectacle lens housed in a frame to be held in front of the eye. An ophthalmic lens can provide refractive eye correction to a lens wearer, ie, a patient, who requires refractive eye correction.

  “Ocular accommodation” means an optical variation of the refractive power of the eye. Typically, eye accommodation refers to the ability of the eye to vary the refractive power of the eye lens by changing the shape of the eye lens. If the patient has no eye adjustment error, the patient will not show an adjustment lag or adjustment lead. The accommodation lag is the amount of the eye's accommodation response that is slower than the photorefractive stimulus that induces accommodation. The accommodation lead is the amount that the eye accommodation response exceeds the photorefractive stimulus that induces accommodation. Although it should be possible to adjust well until it becomes presbyopia, the person's ability to adjust the eye deteriorates over time.

  It is disclosed that a myopic patient (myopic person) has a larger lag of eye accommodation than a normal patient (normal person). The large eye adjustment lag is illustrated by the fact that the adjustment error is larger than the adjustment error of the normal viewer. Adjustment errors are zero in patients without adjustment leads or adjustment lag. Similarly, the adjustment error for patients with adjustment lag is negative and the adjustment error for patients with adjustment leads is positive. Measurements of the degree of adjustment error are generally expressed in unit diopters.

  The contact lens methods and applications of the present invention described herein are effective in reducing adjustment errors in patients who can make eye adjustments. Thus, the presbyopic patient, ie presbyopia, has already had reduced or no ability to adjust the eye, so the method and use of the present invention is particularly beneficial for people who are not presbyopic. It is. Most people diagnosed with presbyopia are those aged 40 and older. Thus, the methods and uses of the present invention are beneficial to patients younger than 40 years. In some embodiments, such methods and applications may be useful for pre- and post-age people, minors, or both. For example, the method and application of the present invention are effective in reducing eye adjustment errors and improving eye adjustment accuracy in patients younger than 25 years.

  Conventional instruments and methods known to those skilled in the art may be used to measure the accommodation error. For example, in order to measure the ocular accommodation response at several different distances such as a near vision distance, an intermediate vision distance, or a far vision distance, a detector or a refractometer may be employed. An example of a detector that can be used is the ELITE detector available from WelchAllyn (Skanee Tols Falls, NY, USA), and an example of a refractometer that can be used is Grand Seiko. It is WR-5100K which can be purchased from (Grand Seiko: Fukuoka Prefecture). Additional detectors that can be used are available from companies such as Keeler and Heine. In the clinical environment, at least one eye accommodation error measurement is made at a short distance, eg 40 cm, and at least one eye at a long distance, eg 6 m (600 cm), ie virtually infinite. An adjustment error measurement is made. Specific examples of visual targets that can be used to measure an accommodation error include several existing visual acuity test tables, such as a Snellen visual acuity test table or a Maltese cross. The eye adjustment error measurement may be performed only once, or an average may be obtained after the eye adjustment error measurement is performed a plurality of times to present a frequency display of the patient's eye adjustment error. The eye accommodation response may be recorded for both eyes or one eye as required. As can be appreciated, eye accommodation is often measured for only one eye because certain aspects of eye function are governed by interlocking muscles. For example, the ophthalmic lens is placed close to the patient's eye. Eye adjustment errors are observed by measuring the eye adjustment error of the eye that is not wearing an ophthalmic lens, while the patient is viewing the eye chart while wearing the ophthalmic lens. become. Specific examples of eye accommodation measurement and eye accommodation error will be described here.

  In carrying out the method of the present invention, an ophthalmic lens is provided. In other words, a method for reducing an eye adjustment error of a patient capable of performing eye adjustment includes providing at least one ophthalmic lens. As used in this case, the indefinite article 'a' or 'an' in an English source means one, one, one kind, one or more, and 'at least one', It can be replaced by the phrase “at least one”. The ophthalmic lens will be deployed for the patient's eye capable of adjusting the eye and for the eye where adjustment error improvement is desired. The ophthalmic lens is deployed on the patient's eye so that light passes through the lens and reaches the retina of the eye. When the ophthalmic lens is a contact lens, the contact lens is placed on the corneal epithelium of the eye so that the back surface of the contact lens faces the corneal epithelium.

  The provided ophthalmic lens has a vision correction area and a myopic defocus area. As used herein, the vision correction area comprises one or more areas that can be visually identified, or the myopic defocus area comprises one or more areas that can be visually identified, Alternatively, both the visual acuity correction area and the myopic focal blur area include one or a plurality of areas that can be visually identified. It is better to understand that the visual acuity correction area is a part of an ophthalmic lens that performs visual acuity correction such as visual sensitivity correction. It is understood that the myopic defocus area is the part of an ophthalmic lens that causes myopic defocus on the lens wearer's eye. A plurality of different areas of the vision correction area, a plurality of different areas of the myopic defocus area, or a plurality of different areas of both areas are arranged in a variety of different configurations. Furthermore, it can be seen that the vision correction area and the near vision defocus area of the ophthalmic lens delimit the optical area of the ophthalmic lens. Or, in other words, the optical area of the ophthalmic lens may include a vision correction area and a near vision defocus area as essential requirements.

  The vision correction area of the ophthalmic lens exhibits a refractive power that corrects the distance vision of the patient's eye. Therefore, it can be seen that the visual acuity correction area of the ophthalmic lens has a far light refractive power, a far refractive power, or a far vision refractive power. In embodiments, the refractive power of the vision correction area is from about 0 diopters to about -10.0 diopters. This contrasts with the refractive power that corrects the near vision of the eye, or contrasts with a region that has near light power, near power, or near vision power It is. The configuration of the vision correction area of the lens of the present invention, i.e., the configuration of the region exhibiting the far-light refractive power (size, shape, or both size and shape) is clear to the patient at both near and far viewing distances. It is set to bring visible vision. Therefore, the visual acuity correction area may exhibit spherical refractive power, cylindrical refractive power or cylinder refractive power, or both spherical refractive power and cylindrical refractive power. The optical power in the vision correction area of the ophthalmic lens is provided by the curvature of the spherical lens surface, the curvature of the aspheric lens surface, or various combinations of both. As used herein, the vision correction area may exhibit an effective single refractive power. That is, the vision correction area of an ophthalmic lens may appear to have only one type of refractive power when measured by a vertex meter or focal length meter as used in contact lens manufacturing environments. is there. However, the vision correction area may have an aspheric surface that provides more than one type of refractive power to the vision correction area, in which case the lens still exhibits only one type of refractive power that is effective. .

  As used herein, “short distance (near target distance)” means a visual distance that the distance at which the target is viewed is about 60 cm or less from the patient. The viewing distance may be referred to as a target distance. Specific examples of myopic distance include about 50 cm, about 40 cm, about 35 cm, and about 25 cm. In certain embodiments of the present disclosure, near vision is often measured at about 40 cm. “Far distance (distance)” as used in this case means a viewing distance or a visual distance when the distance at which the visual target is viewed is at least 400 cm. Specific examples of hyperopic distances include at least 400 cm, at least 500 cm, and at least 600 cm. The “intermediate viewing distance (intermediate visual target distance)” as used in this case means a distance between the near visual target distance and the far visual target distance. For example, the intermediate visual target distance means a distance from about 61 cm to about 399 cm, and specific examples include distances such as about 80 cm, about 100 cm, about 120 cm, and about 140 cm. Is mentioned.

  In view of the above, the vision correction area of the ophthalmic lens of the present invention has a refractive power that provides a visual acuity visible to the patient at a target distance shorter than about 60 cm and a distance from about 400 cm to infinity. I understand that. The vision correction area of the ophthalmic lens of the present invention provides visual acuity that is clearly visible to the patient at intermediate target distances or intermediate visual distances.

  In contrast, various commercially available bifocal contact lenses are not described as including a far vision area that provides a clear vision at both near and far distances. Instead, commercially available bifocal contact lenses, such as the ACUVUE bifocal contact lens from Johnson & Johnson, provide a far vision range that provides clear vision at long distances. And a near vision area that provides clear vision at close range. Thus, the two types of refractive power of a bifocal contact lens provide a clear visual acuity by utilizing two different regions of the lens (ie, the far vision region and the near vision region). The Accuview bifocal contact lens has an 8 mm diameter optical zone composed of a central far vision zone with a diameter of 2 mm and five alternating near and far vision zones that surround the central far vision zone. . These different viewing zone dimensions are important because the Accuview bifocal contact lens provides more distance vision correction in the far viewing area while looking at the far distance and while looking at the near distance. This is because sufficient near vision correction is performed in the near vision region.

  In contrast to this, the vision correction area of the ophthalmic lens of the present invention is set so as to exhibit far-light refracting power and to provide visual acuity whose structure is clearly visible at both distances. In other words, the patient uses only the far-light power of the ophthalmic lens to obtain visual acuity that is clearly visible at both near and far viewing distances. This is due, at least in part, to non-presbyopic patients equipped with the ophthalmic lens of the present invention so that they can fully adjust their eyes while looking nearby. The fact is that you can see nearby targets effectively without compromising on the direction to cancel your vision. When using a lens with a far vision area of smaller dimensions, patients need to use that near vision area with bifocal lenses such as Accuview bifocal contact lenses to see clearly at close range It is predicted that

  As described above, the ophthalmic lens of the present invention has a myopic defocus area. The refractive power in the near vision defocus area is different from the refractive power in the vision correction area. The myopic defocus area configuration (size, shape, or both size and shape) is set to provide a myopic defocus image to the patient when viewed at both near and far viewing distances. At the same time, the vision correction area, i.e., the area having the far-light refractive power, provides a visual acuity to the patient.

  “Myopia defocus” as used herein refers to a defocused image formed on the front side of the retina by an ophthalmic lens. It can be seen that the myopic defocus is “positive” in that the position of the defocus image generated by the ophthalmic lens is in front of the retina of the eye on which the ophthalmic lens is acting.

  The refractive power in the near vision defocus area is usually less negative than the refractive power in the vision correction area. For example, if the refractive power of the vision correction area is about -10 diopters, the refractive power of the near vision defocus area is about -9.0 diopters, about -8.0 diopters, about -7.0 diopters, about -6.0 diopters, about -5.0 diopters. , About -4.0 diopters, about -3.0 diopters, about -2.0 diopters, about -1.0 diopters, or about 0.0 diopters. The refractive power of the vision correction area of the ophthalmic lens of the present invention can be between about 0 diopters to about −10.0 diopters, and the refractive power of myopic defocus is about 2 diopters plus the refractive power of the vision correction area. Get closer. The refractive power in the near vision defocused area is less negative than the refractive power in the vision correction area (whatever the diopter value is). The refractive power of the myopic defocus area can be a negative diopter value, a 0 diopter value, or a positive diopter value. A patient equipped with the ophthalmic lens (one or two) of the present invention uses the far vision area to see clearly at both distances, so that the patient has a myopic focus to obtain clear vision at close distances. No blur area is used (as opposed to the near vision area of commercially available bifocal contact lenses); instead, the near vision focus area provides a defocused image to the patient at both the near and near distances. It is important to be effective in producing a clear image.

  The ophthalmic lens can also provide near vision defocus that causes the myopia defocus of the eye to differ between the distance and the near vision distance. For example, the myopic defocus of the eye at near vision distance differs from the myopic defocus of the eye at hyperopic distance by a diopter value that is less than or equal to the patient's eye adjustment error. For example, if the amount of central myopic defocus at hyperopic distance is about +2 diopters, and the patient's eye adjustment lag is about -0.75 diopters at myopic distance, the central myopic defocus will be Is approximately +1.25 diopters at near vision distance, and the difference between central myopic focus blur at near vision distance and central myopia focus blur at far vision distance is approximately +0.75 diopter. Similarly, the degree of accommodation lead present in the patient's eye can affect the degree of myopic defocus experienced by the patient at both near and near viewing distances.

  If the ophthalmic lens of the present invention described herein is provided to a lens wearer, i.e., a patient, capable of adjusting the eye, the ophthalmic lens is applied to the patient's eye for the purpose of correcting vision. When deployed, it is observed that patient adjustment errors are reduced. This reduction of eye accommodation error is in contrast to the eye error seen in patients who have not examined the eye lens but have been corrected for distance vision. In some situations, this reduction in eye adjustment error is an adjustment that can be seen in patients who have undergone inspection while wearing a single vision eye lens that does not have a myopic focal blur area but has a myopic area. It is also in contrast to the error.

  The vision correction area, myopic defocus area, or both areas, as described herein, have multiple secondary areas or secondary areas that are included as essential requirements or are It may be included as a part.

  Therefore, it can be seen that one aspect of the present invention relates to the use of the ophthalmic lens described above for the purpose of reducing the patient's eye accommodation error. Accordingly, the present invention relates, in part, to the use of contact lenses that are provided with a vision correction area and a myopic defocus area as described herein to reduce patient accommodation errors. is doing.

  One aspect of the present invention is a method for reducing an eye adjustment error of a patient, comprising the step of providing an ophthalmic lens as described above, wherein the ophthalmic lens is not worn but the distance vision is When an ophthalmic lens is attached to a patient's eye for the purpose of correcting vision, the patient's adjustment error is reduced compared to the adjustment error seen in patients who have been examined in a fully corrected state. Can be observed. As a means for sufficiently correcting the distance vision of the eye to be compared with respect to some effects of the ophthalmic lens, a second lens, for example, a spectacle lens, is used instead of using an ophthalmic lens that reduces the adjustment error. There may be the use of different contact lenses or other types of lenses, or even correction is achieved by mathematical methods. Such reduction methods include the step of providing a contact lens provided with a vision correction area and a myopic defocus area, as described herein, in which case the contact lens is not worn but is distant vision. When the contact lens for correcting vision is worn on the patient's eyes compared to the adjustment error seen in patients who have been examined in a fully corrected state, Reduction is observed.

  Specific examples of adjustment error reduction include adjustment lug reduction, adjustment lead reduction, or both. For example, if a patient shows an adjustment lug of about -1.5 diopters with the lens of the present invention attached, the adjustment lug will be less negative than about -1.5 diopters, i.e., greater than positive. There is. For example, the adjustment lag may be reduced from -1.5 diopters to -1.2 diopters and reduced to values such as -1.0 diopters, -0.75 diopters, -0.5 diopters. If the adjustment error with the lens of the present invention is observed to be about 0 diopters, the patient's adjustment error has already been corrected, i.e., has been treated.

  FIG. 1 illustrates one embodiment of an ophthalmic lens according to the present invention. In this embodiment, the ophthalmic lens 10 is a contact lens. The lens 10 is provided with a vision correction area 12 and a defocus area 14. The vision correction area 12 and the near vision defocus area 14 delimit the optical area 16 of the lens 10. The optical region 16 is surrounded by a non-optical peripheral region 18, and the non-optical peripheral region 18 extends from the outer periphery of the optical region 16 of the lens 10 to the peripheral edge region 20. As can be appreciated from FIG. 1, the optical zone 16 comprises or consists of a plurality of concentric rings surrounding a central circular zone.

  In the lens 10 illustrated in FIG. 1, a central area 22 is provided in the vision correction area 12. As described in the present case, the central region 22 exhibits a far light refractive power. The central area 22 is arranged in the center around the optical axis 24 of the lens 10. The central region 22 is illustrated as being circular or substantially circular. The diameter of the central area of the contact lens is greater than 2.0 mm. The diameter of the central region 22 is determined by measuring the linear distance from the contact lens in the two-dimensional front plan view through the optical axis 24 to the opposing outer edge boundaries of the central region 22. The contact lens may have a central region 22 exhibiting far-light refractive power and a diameter of at least 2.3 mm. The contact lens may have a central area 22 exhibiting a far-light refractive power and a diameter of at least 2.5 mm. The contact lens may have a central region 22 exhibiting far-light refractive power and a diameter of at least 3.3 mm. The central region 22 of the contact lens exhibits far-light refractive power and may have a diameter larger than 4.0 mm.

  The lens 10 illustrated in FIG. 1 includes an annular region 26 that surrounds a central circular region 22. The annular region 26 is a region of a single refractive power, so that it may appear as a single ring when viewed using an optical instrument, or it may be a single region that exhibits multiple refractive powers. The annular region 26 may appear to have a plurality of secondary rings. In FIG. 1, the annular region 26 comprises a plurality of concentrically arranged secondary rings 26a, 26b, 26c, which are included as a requirement or included as part of the component. Therefore, in the contact lens provided by the method of the present invention, the contact lens is provided with a myopic defocus area, which is adjacent to and surrounds the circular central area 22. It can be seen that it includes a first annular zone, such as a ring 26a, which is included as a prerequisite or as part of the component. As an alternative or in addition, a contact lens as illustrated in FIG. 1 comprises an annular area 26 surrounding a circular central area 22, which is concentric. A plurality of annular secondary rings 26 a, 26 b, 26 c arranged in a shape, and at least one of these secondary rings, for example, the secondary ring 26 a, becomes a part of the myopic focal blur region 14. In addition, at least one of the secondary rings, for example, the secondary ring 26b, is a part of the vision correction area 12. For purposes of this disclosure, the refractive power of the secondary ring approximates the refractive power of the vision correction area 12 (eg, within 20% or within 0.25 diopters), or If they are the same, the secondary ring is part of the vision correction area 12, or the refractive power of the secondary ring approximates the refractive power of the myopic defocus area 14 (for example, within 20%). Or within the range of 0.25 diopters), or if they are identical, the secondary ring is part of the myopic defocus area 14. In FIG. 1, the lens 10 includes a secondary ring 26 c that is part of the myopic defocus area 14. The diameter of the optical zone 16 is typically 9.0 mm or less. For example, the diameter of the optical zone may be about 8.0 mm. The width of the annular zone corresponds to the value obtained by dividing the difference between the optical zone diameter and the central zone diameter by two. For example, if the optical zone diameter is 8.0 mm and the central zone diameter is 3.0 mm, the width of the annular zone is 2.5 mm. As long as the annular zone does not extend beyond the outer edge of the optical zone, the width of each secondary ring may vary by any value.

  FIG. 2 illustrates a further embodiment of an ophthalmic lens according to the present invention. The lens 30 includes a central circular area 32, a first annular area 34, and a second annular area 36. The lens 30 has a vision correction area and a myopia focus blur area, and a transition area is provided between the vision correction area and the myopia focus blur area. As an example, the central circular area 32 is a part of the vision correction area, the first annular area 34 is provided with a transition area, and the second annular area is a part of the myopic defocus area. In the alternative, the central circular area 32 is part of the myopic defocus area, the first annular area 34 comprises a transition area, and the second annular area is part of the vision correction area. The central circular zone 32, the first annular zone 34, and the second annular zone 36 delimit the optical zone 38 of the lens 30. The optical region 38 is surrounded by a non-optical peripheral region 40, and the non-optical peripheral region 40 extends from the outer outer side of the optical region 38 to the peripheral edge region 42 of the lens 30.

  In the lens 30 illustrated in FIG. 2, the visual acuity correction area includes a central area 32. As described in this case, the central region 32 exhibits a far-light refractive power. The central region 32 is illustrated as being circular or substantially circular. In the method of the present invention, the central area of the contact lens may have a diameter greater than 2.0 mm. The diameter of the central region 32 is determined by measuring the linear distances that reach the mutually opposing peripheral boundaries of the central region 32 through the optical axis 44 in the two-dimensional front plan view of the contact lens. The contact lens may have a central area 32 exhibiting a far refracting power and a diameter of at least 2.3 mm. In some cases, the central region 32 of the contact lens exhibits far-light refractive power and has a diameter of at least 2.5 mm. The contact lens may have a central area 32 exhibiting a far refracting power and a diameter of at least 3.3 mm. The contact lens may have a central region 32 exhibiting far-light refractive power and a diameter of at least 4.0 mm.

  The lens 30 illustrated in FIG. 2 may include a first annular region 34 that surrounds a central circular region 32. In FIG. 2, the first annular region 34 includes an aspherical transition region. When the central circular area 32 has a vision correction area, and the second annular area 36 has a myopic focal blur area, the first annular area 34 is a vision correction on the inner inner peripheral side of the annular area 34. An aspherical transition region from the outer region to the near-focus focal blur region on the outer outer side of the annular region 34. Similarly, when the central circular area 32 includes a myopic focal blur area and the second annular area 36 includes a vision correction area, the first annular area 34 is on the inner inner peripheral side of the annular area 34. An aspherical transition region from the near vision defocusing region to the vision correction region on the outer outer side of the annular region 34 is provided. In addition, the central circular area 32 may be aspheric over its diameter, the first annular area 34 may be aspheric, and the second annular area may be aspheric. Alternatively, each region may be aspherical by various combinations thereof.

  In the present invention, the method of the present invention is effective in producing an eye accommodation error of less than +1.5 diopters and greater than -1.5 diopters when the patient is looking at a target distance of only about 60 cm.

  In the present invention, the method of the present invention is effective in producing an eye accommodation error of less than +1.5 diopters and greater than −1.5 diopters when the patient is viewing at a target distance of 60 cm to about 400 cm. Become.

  In the present invention, the vision correction area needs only one type of refractive power to correct the patient's distance vision, and the vision correction area has a visual acuity that is clearly visible to the patient at a target distance of less than 60 cm. The myopic defocused area results in myopic defocus at the same time that the patient sees a clear near-field image at that target distance. “Clear visual acuity” as used in the present case is usually determined by a vision inspector who performs a visual acuity test in such a way as to use a standard character chart. In disclosing the present case, “clear visual acuity” means a case where the lens wearer wears the contact lens of the present invention, and is viewed at a distance target distance such as a target distance of 600 cm. May be considered to mean that the visual score is about 20/40 to about 20/10.

  For any of the methods of the present invention, “donate” means supplying the lens to a lens distributor, providing the lens to a vision corrector such as an optometrist or ophthalmologist, and preparing the lens for the patient. Or a combination of these. The method of the present invention may be directed to lens manufacturers that provide ophthalmic lenses to lens distributors such as lens retailers that supply stock lenses to vision correctors and patients. The method of the present invention may be directed to lens manufacturers or lens distributors that provide ophthalmic lenses to vision examiners. Such a method may be aimed at a vision acupuncturist who prepares a lens for the patient and instructs the patient how to wear the lens.

  In the present invention, the “donating” step provides the eye lens to the eye examiner so that the eye of the patient wearing the eye lens on, in or near the eye. It is included as one specific example that the eyesight inspector or the eye inspector observes the adjustment error in FIG. 1. It is included as an essential requirement, and is included as one of the components. Such a method may include another additional step of measuring an accommodation error in the patient's eye. The measuring process is carried out by an eye inspector, a person working with the eye inspector, a person employed by the eye inspector, or a machine.

  Among other methods, for example, in the methods described up to the previous stage, the “donating” step supplies the lens to a lens distributor, and provides the lens to a vision corrector such as an optometrist or an ophthalmologist. Including preparing the lens for the patient, or various combinations thereof. Furthermore, among other methods, for example, in the methods described in the preceding paragraph, the “donating” step supplies the lens to a lens distributor, and corrects the eyesight such as an optometrist or an ophthalmologist. Including providing the doctor, preparing the lens to the patient, or various combinations thereof.

  For any of the methods of the present invention, the step of “donating” includes providing a first lens and a second lens. When the lens is a contact lens, “donating” means providing a plurality of lenses in the first box or a plurality of lenses in the first box and the second box. Including that.

  The contact lens of the present invention provided by the method of the present invention may be a soft contact lens, that is, when the contact lens of the present invention is placed in the lens wearer's eye, the contact lens of the lens wearer has a shape of the eye. It is a contact lens having a degree of flexibility that approximately matches. A soft contact lens is a lens that does not break even if it is bent so as to overlap. Typically, soft contact lenses are referred to as hydrogel contact lenses compared to rigid gas permeable contact lenses. The term “hydrogel contact lens” as used herein refers to a polymer lens that has the ability to absorb water and maintain water in equilibrium. In the context of the description herein, the hydrogel lens may be a polymer material that does not contain a silicone-containing component, or it may be a polymer material that contains a silicone-containing component. The majority of hydrogel contact lenses that do not contain silicone are based on polymerisable lens formulations containing various monomers of hydroxyethyl methacrylate (HEMA). Specific examples of hydrogel contact lens materials include those having the US Certified Substance Name (USAN) listed below. That is, etafilcon A, nelfilcon A, occufilcon A, occufilcon B, occufilcon C, ocfilfilcon D, and omafilcon A (English names: etafilcon A, nelfilcon A, ocufilcon A, ocufilcon B, ocufilcon B, ocufilcon B C, ocufilcon D, omafilcon A). In addition to this, the contact lens of the present invention may be a hydrogel contact lens mainly containing a lens composition containing glyceryl methacrylate (GMA) alone or containing GMA as a mixture with HEMA. . Silicone-containing hydrogel contact lenses are often referred to as silicone hydrogel contact lenses. Most silicone hydrogel contact lenses are based on polymerizable lens formulations such as various monomers of siloxane, various low weight materials, or various polymer monomers. Specific examples of the silicone hydrogel contact lens material include substances having the names of US-listed substances listed below. That is, aquafilcon A, barafilcon A, comfilcon A, enfilcon A, galifilcon A, renefilcon A, lotrafilcon A, lotafilcon B, and senofilcon A (English name: acquafilcon A or aquafilcon A in order, balafilcon A, comfilcon A, enfilcon A, galyfilcon A, lenefilcon A, lotrafilcon A, lotrafilcon B, senofilcon A).

  The contact lens of the present invention comprises one or more hydrophilic monomers, one or more hydrophobic monomers, one or more silicone-containing monomers, one or more silicone-containing low weight bodies, and one or more types. It may be a polymerization reaction product of a polymerizable composition comprising a silicone-containing polymer monomer, one or more polymers, or various combinations thereof. In addition, specific examples of the polymerizable composition used to produce the lens of the present invention include a crosslinking agent, a free radical polymerization initiator, a colorant, and an ultraviolet absorber. The soft contact lens of the present invention is composed of any of the above-mentioned contact lens materials identified by the above-mentioned United States Certified Substance Name (USAN), and includes any of these as essential elements. Is included as part of it. The lens of the present invention may be made from omafilcon A. In other embodiments, the lens of the present invention may be a silicone hydrogel contact lens made from Comfilcon A or Enfilcon A.

  The contact lens of the present invention may be a molded contact lens such as a rotationally molded contact lens or a cast molded contact lens, or may be a lathe rotationally processed contact lens. It can be seen that these various contact lenses have different physical characteristics due to their manufacturing methods. A “cast molded contact lens” is a contact lens obtained from a contact lens mold assembly that is constructed by bringing two contact lens mold pieces into contact with each other to form a contact lens shaped cavity. In addition, a part of the contact lens of the present invention is polished or smoothed after the contact lens is formed. For example, contact lenses that have been cast or turned, or contact lenses that have been both cast and turned, can be polished to reduce transition areas, or edges The shape can be improved, resulting in better comfort compared to a lens that has not been polished.

  The contact lens of the present invention may be a daily wearing lens or a lens worn for a long time. As used in the present invention, a long-wearing contact lens refers to a contact lens that has been approved for wearing over 24 hours in a row. Each contact lens forming a pair of lenses is a contact lens that can be disposable in one day (that is, a contact lens that is disposed only once in a human eye). Compared to this, as will be appreciated by those skilled in the art, the daily wear lens is worn on the human eye and then washed and attached to the human eye at least once more. One-day disposable contact lenses are physically different, chemically different, or physically and chemically different when compared to daily and long-wear contact lenses Yes. For example, the prescription used to make daily or long-wearing contact lenses is different from the prescription used to make one-day disposable contact lenses, This is due to economic and commercial factors in producing a fairly large amount of one-day disposable contact lenses.

  When the contact lens of the present invention is placed on the patient's eye, the back of the lens faces the corneal epithelium of the patient's eye. A corneal onlay lens, a corneal inlay lens, an intraocular lens, or the like is placed in the eye by surgery. The spectacle lens is deployed in front of the patient's eye.

  In another embodiment, a method for reducing an adjustment error of a patient capable of performing eye adjustment includes the step of providing a contact lens adapted to be placed in a patient's eye capable of performing eye adjustment. It includes or has such a process as one of the constituent elements. Such a contact lens has a vision correction area and a myopic defocus area. The vision correction area exhibits refractive power that corrects the distance vision of the patient's eye and is configured to provide vision that is clearly visible to the patient at both near and far viewing distances. The vision correction area has a central circular area with a diameter larger than 2.0 mm. The near-focus defocus area has a refractive power different from that of the vision correction area, and when the vision correction area has a visual acuity that is clearly visible to the patient, the image is out of focus at both near and near viewing distances. Is provided to the patient. The myopic defocus area is provided in one or more annular areas surrounding the central circular area. Such contact lenses are effective to ensure that the patient exhibits an adjustment lag of less than -1.5 diopters. In the present invention, the contact lenses of the present invention may be effective in causing the patient to exhibit an adjustment lag of less than -1.0 diopters. The contact lens of the method of the present invention may be effective in causing the patient to exhibit an adjustment error of about -0.5 diopters to about +0.5 diopters. In yet another embodiment, the contact lenses of the present invention may be effective to cause the patient to exhibit an adjustment error of at least 0.5 diopters, at least 1.0 diopters, or at least 1.5 diopters. The contact lenses of the present invention are effective to ensure that the patient exhibits an adjustment lag of at least 0.5 diopters, at least 1.0 diopters, or at least 1.5 diopters.

  In light of the present disclosure, it can be seen that each aspect of the invention relates to the manufacture of ophthalmic lenses.

  In some contexts, aspects of the present invention provide for the use of lens-forming materials, such as polymerizable compositions, in the manufacture of ophthalmic lenses for reducing accommodation errors for patients capable of performing eye accommodation. Related to the application. This case describes an ophthalmic lens, and it can be seen that an ophthalmic lens so manufactured has a vision correction area and a near vision defocus area, but in this case the vision correction area is far away from the patient's eye. It has refractive power to correct vision and is configured to provide visual acuity to the patient at both near and far viewing distances. It is different from refractive power, and it is configured to bring a defocused image to the patient at the same time when viewed from both near and near viewing distances when the vision correction area has clear vision to the patient. If the ophthalmic lens is deployed on the patient's eye for the purpose of correcting vision, it is observed that the patient's adjustment error is reduced. Lens but not yet worn but is in contrast to the eye for the error seen in patients who received Kenbun in a sufficiently corrected state for distance vision.

  In another context, an aspect of the invention relates to a method of manufacturing an ophthalmic lens for reducing a patient's eye accommodation error that can be accommodated. Such methods include the step of forming a lens-forming material into an ophthalmic lens that is deployed in a patient's eye capable of performing eye accommodation. Such an ophthalmic lens has a vision correction area and a myopic defocus area, and in this case, the vision correction area exhibits a refractive power that corrects the distance vision of the patient's eye and can be used at both near and near vision distances. Constructed to provide clear visual acuity to the patient, the myopic defocus area has a refractive power that is different from the refractive power of the visual correction area, and the visual correction area provides clear visual acuity to the patient Sometimes configured to provide a patient with a myopic defocus image at both near and far viewing distances, in which case an ophthalmic lens is deployed to the patient's eye for the purpose of correcting vision In some cases, it is observed that the patient's adjustment error is reduced, but this reduction of the eye adjustment error is not seen when the ophthalmic lens is worn but the distance vision is corrected sufficiently. In contrast to the eye for the error found in.

  If the ophthalmic lens is a cast molded contact lens, the molding process casts a polymerizable composition into a contact lens shape and separates the cast molded lens from the contact lens mold member. The separated cast molding contact lens is contacted with the liquid, the separated cast molding contact lens is inspected, the separated casting molding contact lens is packed in the contact lens packing material, and the contact lens is sterilized together with the packaging material. Or performing various combinations of these processes.

  One method of making a cast molded contact lens is as follows. A first mold member and a second mold member are manufactured. The first mold member and the second mold member are configured to form a contact lens type assembly when coupled together. The first mold member is a front mold member and has a concave lens forming surface that forms the front side of the contact lens. The second mold member is a back-side mold member, and has a convex lens forming surface that forms the back side of the contact lens. The first mold member is manufactured so as to exhibit one or more types of surface curvature on its concave surface. The dimension of the surface curvature is set so as to provide a visual acuity correction area and a myopic defocus area as described herein. Polymerizable compositions are manufactured and contain various reactive materials and optionally various non-reactive materials used in molding contact lenses. Specific examples of these various materials include one or more types of hydrophilic monomers, hydrophilic low-weight materials, hydrophilic polymer monomers, hydrophilic polymers, one or more types of hydrophobic monomers, and hydrophobic properties. Low weight bodies, hydrophobic polymer monomers, hydrophobic polymers, or any combination thereof. The polymerizable composition is dispensed on the concave surface of the first mold member. The second mold member is placed in contact with the first mold member to form a contact lens mold assembly that allows the polymerizable composition to be placed inside a contact lens shaped cavity. The contact lens mold assembly is then exposed to heat or light to form a polymerized contact lens product by polymerizing the polymerizable composition. To disassemble the contact lens mold assembly mold, the first mold member and the second mold member are separated from each other. Since the polymerized contact lens product remains attached to the first mold member and the second mold member, the lens is then removed or separated from the mold member. The removed contact lens is brought into contact with a liquid, which may be a cleaning liquid or a packaging liquid. In some methods, the cleaning solution includes one or more agents that help extract unreacted or partially reacted material from the removed contact lens product. Such methods may include one or more steps of inspecting the lens in a dry state, a moisturized state, or both. Such inspection may include defect inspection and quality control inspection. If the lens is placed in a packaging liquid, it is preferable to sterilize after the packaging material is sealed.

  In view of the description up to the previous stage, it can be seen that still another aspect of the present invention includes the matters described below. Each of the details described up to the previous stage applies to any one or more of the following embodiments and still falls within the scope of the present invention.

  One aspect of the present invention is an eye as an adjustment error reduction device that is effective when deployed in a patient's eye for the purpose of providing visual acuity correction to the patient's eye that is capable of performing eye adjustment and has symptoms of adjustment error. The present invention relates to the use of a lens for use. The effect of reducing the adjustment error is in contrast to the ophthalmic error seen in patients who have not been wearing an ophthalmic lens but who have been examined with the distance vision corrected sufficiently. The ophthalmic lens used has a vision correction area and a myopic defocus area or is included as part of a component, in which case the vision correction area is a refractive that corrects the distance vision of the patient's eye. And its configuration (ie, size, shape, both size and shape, etc.) is set to provide visual acuity to the patient at both near and far viewing distances, and myopia The defocus area has a refractive power different from that of the vision correction area, and its configuration (ie, size, shape, both dimensions and shape, etc.) has a visual acuity that is clearly visible to the patient by the vision correction area. It is set to provide a myopic defocus image to the patient when viewed at both near and far viewing distances. One aspect of the present invention can also be considered to be the use of an ophthalmic lens to reduce eye accommodation in a patient who is able to perform eye accommodation and yet has symptoms of eye accommodation error. The ophthalmic lens used is a contact lens.

  Another aspect of the present invention is the use of an ophthalmic lens for reducing eye adjustment errors in a patient who is able to make eye adjustments and still have symptoms of adjustment errors. The ophthalmic lens used has a vision correction area and a myopic defocus area, or is included as part of a component, in which case the vision correction area is a refractive power that corrects the vision of the patient's eye. And its configuration (ie, size, shape, both size and shape, etc.) is set to provide clear vision to the patient at both near and far viewing distances, and the myopic focus The bokeh area has a refractive power different from that of the vision correction area, and its configuration can be viewed at both near and far viewing distances when the vision correction area provides clear vision to the patient. Is also set to provide a myopic defocus image to the patient. Such an ophthalmic lens may be a contact lens.

  Another aspect of the present invention is an ophthalmic lens that can be used to reduce eye adjustment errors in a patient that is capable of eye adjustment and that has symptoms of adjustment errors. Such ophthalmic lenses have a vision correction area and a myopic defocus area, or are included as part of a component, in which case the vision correction area is a refractive power that corrects the distance vision of the patient's eye. And its configuration (ie, size, shape, both size and shape, etc.) is set to provide clear vision to the patient at both near and far viewing distances, and the myopic focus The blurred area has a refractive power different from that of the vision correction area, and its configuration (ie, size, shape, both dimensions and shape, etc.) provides visual acuity that is clearly visible to the patient by the vision correction area. When viewed at both near and far viewing distances, the patient is set to produce a myopic defocus image. Such an ophthalmic lens may be a contact lens.

  Another aspect of the present invention is a lens for use in manufacturing an ophthalmic lens for reducing eye adjustment errors in a patient who is capable of eye adjustment and is symptomatic of adjustment errors. Forming material. Such ophthalmic lenses have a vision correction area and a myopic defocus area, or are included as part of a component, in which case the vision correction area is a refractive power that corrects the distance vision of the patient's eye. And its configuration (ie, size, shape, both size and shape, etc.) is set to provide clear vision to the patient at both near and far viewing distances, and the myopic focus The blurred area has a refractive power different from that of the vision correction area, and its configuration (ie, size, shape, both dimensions and shape, etc.) provides visual acuity that is clearly visible to the patient by the vision correction area. When viewed at both near and far viewing distances, the patient is set to produce a myopic defocus image. Such an ophthalmic lens may be a contact lens.

  Still another aspect of the present invention is an ophthalmic lens that is employed when manufacturing an ophthalmic lens that can reduce the adjustment error of the eye of a patient who can adjust the eye and has symptoms of the adjustment error. It is a design. Such ophthalmic lenses have a vision correction area and a myopic defocus area, or are included as part of a component, in which case the vision correction area is a refractive power that corrects the distance vision of the patient's eye. And its configuration (ie, size, shape, both size and shape, etc.) is set to provide clear vision to the patient at both near and far viewing distances, and the myopic focus The blurred area has a refractive power different from that of the vision correction area, and its configuration (ie, size, shape, both dimensions and shape, etc.) provides visual acuity that is clearly visible to the patient by the vision correction area. When viewed at both near and far viewing distances, the patient is set to produce a myopic defocus image. Such an ophthalmic lens may be a contact lens.

  Each aspect of the present invention can be better understood by contemplating subsequent embodiments.

  A hydrogel contact lens is provided as illustrated in FIG. Such a contact lens is a cast-molded contact lens made of omafilcon A as a raw material as already described in the description up to the previous stage. The center area of the contact lens has a far light refractive power. The diameter of the central region of the hydrogel contact lens is about 3.3 mm and the refractive power of the central region is -3.00 diopters. The diameter of the secondary ring corresponding to the secondary ring 26a is 4.8 mm (including the central region), and its refractive power is -1.00 diopter. The diameter of the secondary ring corresponding to the secondary ring 26b is 6.8 mm, and its refractive power is −3.00 diopters. The diameter of the secondary ring corresponding to the secondary ring 26c is 9.0 mm (including the central region), and its refractive power is -1.00 diopter.

  The eye adjustment error measurements of 13-year-old myopia were recorded. Measurements were made using a refractometer or detector at a target distance of 40 cm and a target distance of 600 cm. The measurement was performed on the patient's left eye in a state in which the distance vision was sufficiently corrected even when the lens was not worn, and in a state in which the contact lens was worn. The measurement data is illustrated in FIG. The patient experienced a reduction in adjustment error when the lens was worn compared to when the lens was not worn.

  While this disclosure refers to certain specific embodiments, it is to be understood that these embodiments have been presented by way of illustration and not limitation. The intention of the foregoing detailed description is that specific embodiments have been discussed, but it is intended to cover all modifications, alternatives, and equivalents of each embodiment, including the appended patents. It should be construed as falling within the spirit and scope of the invention as defined in the claims.

Claims (17)

A method for reducing an eye adjustment error of a patient capable of performing eye adjustment,
Providing an ophthalmic lens that is deployed to the patient's eye capable of eye accommodation and includes a vision correction area and a near vision defocus area, the vision correction area being far away from the patient's eye It has a refractive power that corrects visual acuity and is designed to provide a clear visual acuity to the patient at both near and far viewing distances. It is different from refractive power, and it is configured to give the patient a myopic defocus image at both near and far viewing distances if the vision correction area has clear vision for the patient. And
In contrast to the patient's ophthalmic adjustment error, which is not worn but has been corrected for distance vision, the ophthalmic lens is placed against the patient's eye to correct vision. A method wherein, when deployed, reduction of the patient's eye accommodation error is observed.   The method of claim 1, wherein the ophthalmic lens is a contact lens.   3. The method according to claim 2, wherein the vision correction area is provided with a circular area through which the optical axis of the ophthalmic lens passes and whose diameter is larger than 2.0 mm.   4. The method of claim 3, wherein the myopic defocus area is provided with a first annular area adjacent to and surrounding the circular area.   The contact lens is provided with an annular region surrounding the circular region, and the annular region is composed of a plurality of annular secondary rings arranged concentrically, and among the plurality of secondary rings The method of claim 3, wherein at least one of is a part of the myopic defocus area and at least one of the remaining secondary rings is a part of the vision correction area. .   6. Any of claims 1-5, wherein the patient's eye accommodation error is less than +1.5 diopters and greater than -1.5 diopters when the patient is looking at a target distance of only 60 cm. The method of crab.   7. The patient's eye accommodation error is less than +1.5 diopters and greater than −1.5 diopters when the patient is viewing at a target distance of 60 cm to about 400 cm. The method in any one of.   The vision correction area has only one type of effective refractive power to correct the patient's distance vision, and the vision correction area provides clear vision to the patient at target distances of less than 60 cm, 8. A method according to any of claims 1 to 7, characterized in that the myopic defocus area produces myopic defocus at the same time that the patient is viewing a clear near-field image at that target distance. .   The donating includes supplying the ophthalmic lens to a lens distributor, providing the ophthalmic lens to a vision corrector, preparing the ophthalmic lens for a patient, or various combinations thereof. 9. A method according to any of claims 1 to 8, characterized in that   10. The method according to claim 1, wherein the donating includes donating a first lens and a second lens of the ophthalmic lens.   The donating includes providing the ophthalmic lens to a vision inspector, and the eye inspector examines an adjustment error of the eye of the patient in which the ophthalmic lens is provided. The method according to any one of claims 1 to 10.   12. A method according to any preceding claim, further comprising measuring an accommodation error in the patient's eye.   The myopic defocus at nearsighted distance is greater than the patient's eye adjustment error or is different from the myopic defocus at hyperopic distance by a diopter value equal to the patient's eye adjustment error, The method according to any one of claims 1 to 12.   Use of a lens design in manufacturing an ophthalmic lens to reduce an eye adjustment error of a patient capable of performing eye adjustment, the lens design having an eyesight correction area and a near vision defocus area Providing a lens, and the vision correction area is configured to provide refractive power that corrects the distance vision of the patient's eye and to provide vision that is clearly visible to the patient at both near and far vision distances. The myopic defocus area is different in both the near and near viewing distances when its refractive power is different from the refractive power of the vision correction area and the vision correction area provides clear vision to the patient. However, it is configured to bring a myopic defocus image to the patient. And, in the case of mounting the ophthalmic lens to the eye of a patient in order to perform the vision correction, characterized in that the reduction of the accommodation error of the patient is observed, the lens design applications. A method of manufacturing an ophthalmic lens for reducing an eye adjustment error of a patient capable of performing eye adjustment,
Forming a lens-forming material into an ophthalmic lens that is deployed in a patient's eye capable of performing eye accommodation, the ophthalmic lens having a vision correction area and a near vision defocus area; The correction area exhibits refractive power that corrects the distance vision of the patient's eyes, and is configured to provide vision that is clearly visible to the patient at both near and far vision distances. When the power is different from the refractive power of the vision correction area and the vision correction area has clear vision to the patient, it will give the patient a myopic defocus image at both near and near viewing distances Is composed of
In contrast to the ophthalmic error of a patient who has not been ophthalmically worn but has been corrected for distant vision, the ophthalmic lens is applied to the patient's eye for the purpose of correcting vision. A method of manufacturing an ophthalmic lens, characterized in that it is observed that a patient's adjustment error is reduced when deployed.   The molding is performed by casting a polymerizable composition into a contact lens shape, separating the cast lens from the contact lens mold member, and contacting the separated cast molding contact lens with the liquid. Inspect the separated cast molded contact lens, pack the separated cast molded contact lens in the contact lens packaging material, sterilize the contact lens together with the packaging material, or perform various combinations of these treatments. The method according to claim 15, comprising:   The use of an ophthalmic lens for reducing an ophthalmic adjustment error of a patient capable of performing ocular adjustment, wherein the ophthalmic lens has a vision correction area and a myopic defocus area, and the vision correction area is the patient's eye. It is designed to provide a visual power that is clearly visible to the patient at both near and far viewing distances. It is different from refractive power, and it is configured to provide a defocused image to the patient when viewed at both near and far viewing distances when the vision correction area has clear vision to the patient, In contrast to the eye adjustment error of patients who have not been ophthalmically worn but have been corrected for distance vision, the ophthalmic lens is placed on the patient's eye to correct vision. Wearing Case, characterized in that the reduction of the accommodation error of the patient is observed, the ophthalmic lens applications.

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